Biopsy needle suite with hemostasis function

Abstract

The utility model discloses a biopsy needle suite with a hemostasis function, which comprises a coaxial inner needle core component, an energy generating component, an inner insulating layer and a first electrode, the coaxial inner needle core component comprises a coaxial inner needle core and a handle, the coaxial inner needle core is fixedly connected with the handle, the handle is internally provided with the energy generating component, the periphery of the coaxial inner needle core is provided with the inner insulating layer, and the far end of the coaxial inner needle core extends out of the inner insulating layer to form the first electrode; the near end of the coaxial inner needle core is electrically connected with the energy generation assembly; the coaxial outer sleeve assembly comprises a coaxial outer sleeve and an outer sleeve plug, an outer insulating layer is arranged on the periphery of the coaxial outer sleeve, the far end of the coaxial outer sleeve extends out of the outer insulating layer to form a second electrode, the coaxial inner needle core is arranged in the coaxial outer sleeve in a penetrating mode under the hemostasis structure, and the far end of the coaxial inner needle core extends out of the coaxial outer sleeve; the near end of the coaxial outer sleeve is electrically connected with the energy generation assembly; the biopsy needle assembly is used for penetrating through the coaxial outer sleeve to reach a preset position for biopsy sampling; when hemostasis operation is carried out, the energy generation assembly carries out ablation hemostasis on the puncture needle passage through the first electrode and the second electrode.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to a biopsy needle kit with hemostatic function. Background Technology

[0002] Biopsy is a crucial method for tumor diagnosis, and with the continuous rise in tumor incidence, the demand for biopsy procedures is increasing year by year. Statistics show that the global market size for biopsy needles reached several billion US dollars in 2020, and it is expected to maintain rapid growth in the coming years. Biopsy procedures are often accompanied by bleeding, requiring the use of products with hemostatic functions to reduce the risk of bleeding. With the growth of the biopsy market, this invention also possesses significant technical advantages and market prospects.

[0003] There are currently some ablation needle products on the market with hemostatic function, but most of them have the following shortcomings:

[0004] Large size and complex operation: It requires connection to an external radio frequency or microwave host, which increases the difficulty and risk of surgical operation.

[0005] High cost: Radiofrequency or microwave devices are expensive, increasing the cost of surgery.

[0006] Poor hemostasis: Some products have the function of ablation hemostasis, but they cannot accurately locate the biopsy needle path, resulting in poor hemostasis or secondary puncture injury or bleeding (the needle tip is carbonized and adhered at high temperature, and other tissues are torn during the needle withdrawal process, resulting in secondary bleeding). Utility Model Content

[0007] The purpose of this invention is to provide a biopsy needle kit with hemostatic function, which can perform needle tract hemostasis in a timely manner after tissue biopsy. It is simple to operate, low in cost, and highly safe. It does not require the use of expensive emergency medical resources, and can provide accurate diagnosis and treatment for cancer patients with high-risk bleeding, coagulation disorders, etc. It also does not excessively occupy emergency medical resources, thus promoting the healthy use of medical resources.

[0008] The technical solution provided by this utility model is: a biopsy needle kit with hemostasis function, comprising:

[0009] A coaxial inner needle core assembly includes a coaxial inner needle core and a handle. The coaxial inner needle core is fixedly connected to the handle. An energy generating component is disposed inside the handle. An inner insulating layer is disposed on the outer periphery of the coaxial inner needle core. The distal end of the coaxial inner needle core extends out of the inner insulating layer to form a first electrode. The proximal end of the coaxial inner needle core is electrically connected to the energy generating component.

[0010] A coaxial outer cannula assembly includes a coaxial outer cannula and an outer cannula plug. An outer insulating layer is provided on the outer periphery of the coaxial outer cannula. The distal end of the coaxial outer cannula extends out of the outer insulating layer to form a second electrode. In a hemostatic configuration, the coaxial inner needle core is inserted into the coaxial outer cannula and the distal end of the coaxial inner needle core extends out of the coaxial outer cannula. The outer cannula plug is inserted into the handle. The proximal end of the coaxial outer cannula is electrically connected to the energy generating component.

[0011] A biopsy needle assembly is used to pass through the coaxial outer tube to reach a predetermined position for biopsy sampling.

[0012] During hemostasis, the coaxial inner needle core is inserted into the coaxial outer tube, and the energy generating component ablates and stops the bleeding of the puncture needle tract through the first electrode and the second electrode.

[0013] Preferably, it also includes a puncture needle assembly, which is inserted into the coaxial outer sheath and the distal end of the puncture needle extends beyond the distal end of the coaxial outer sheath to puncture to the target location.

[0014] Preferably, the distal end of the coaxial inner needle core is closed, and a thermocouple sensor is provided at the distal end of the coaxial inner needle core. The thermocouple sensor collects the temperature of the distal end of the coaxial inner needle core in real time. When the coaxial inner needle core is inserted into the coaxial outer tube, the inner insulating layer extends out of the distal end of the coaxial outer tube.

[0015] Preferably, the handle is provided with an outer tube socket, and the outer tube plug is electrically connected to the handle by plugging into the outer tube socket.

[0016] Preferably, the energy generating component includes a 12V polymer lithium battery, a high-frequency drive module, a DC-AC module, and a step-up transformer. The 12V polymer lithium battery converts direct current into alternating current through the DC-AC module. The step-up transformer further boosts the converted alternating current and ablates and stops bleeding through the puncture needle tract via the first electrode and the second electrode.

[0017] Preferably, the DC-AC module includes a half-bridge circuit and a resonant circuit. The input terminal of the half-bridge circuit is connected to the high-frequency drive module to provide a drive signal to the DC-AC module. The output terminal of the half-bridge circuit is connected to the input terminal of the resonant circuit, and the output terminal of the resonant circuit is connected to the step-up transformer.

[0018] Preferably, the half-bridge circuit includes a first MOSFET, a second MOSFET, a first Zener diode, a first resistor, a second resistor, a second Zener diode, a third resistor, and a fourth resistor. The first terminal of the first resistor is connected to the signal terminal of the high-frequency drive module. The second terminal of the first resistor is connected to the gate (G) of the first MOSFET. The drain (D) of the first MOSFET is connected to the power supply. The source (S) of the first MOSFET is connected to the drain (D) of the second MOSFET. The first resistor and the first Zener diode are connected in reverse parallel. The anode of the first Zener diode is connected to the resonant circuit through the second resistor. The gate (G) of the second MOSFET is connected to the second terminal of the third resistor. The first terminal of the third resistor is connected to the signal terminal of the high-frequency drive module. The third resistor and the second Zener diode are connected in reverse parallel. The anode of the second Zener diode is connected to the resonant circuit through the fourth resistor.

[0019] Preferably, the resonant circuit includes a first capacitor, a second capacitor, a third capacitor, a fourth capacitor, a fifth capacitor, and a vertical inductor. The first capacitor, the second capacitor, and the vertical inductor are connected in series. The third capacitor is connected in parallel with the first capacitor. The vertical inductor is connected to the fourth capacitor and the fifth capacitor connected in parallel. The first terminal of the fifth capacitor is connected to the first port of the step-up transformer, and the second terminal of the fifth capacitor is connected to the fourth port of the transformer U3.

[0020] Preferably, the handle is provided with an operation button for controlling the on / off state of the energy generating component circuit and a status indicator light for displaying the battery level in the energy generating component.

[0021] Preferably, the high-frequency drive signal output by the high-frequency drive module is greater than or equal to 480kHz.

[0022] Compared with the prior art, the present invention has the following advantages:

[0023] The technical solution of this utility model uses a coaxial outer cannula assembly to both preserve the needle path and form two electrodes with the coaxial inner needle core for needle path ablation and hemostasis. Specifically, after sampling is completed, the sampling needle is withdrawn, while the coaxial outer cannula assembly remains in the needle path to preserve it. The coaxial inner needle core is then inserted into the cannula, thus easily replicating the needle path punctured during sampling. An appropriate current is supplied to the first and second electrodes through an energy generating component, enabling tissue ablation and coagulation, thus preventing needle path bleeding. Attached Figure Description

[0024] Figure 1 This is a schematic diagram of the biopsy needle kit with hemostasis function of this utility model;

[0025] Figure 2This is a schematic diagram of the coaxial inner needle core assembly and the coaxial outer tube assembly of this utility model;

[0026] Figure 3 This is a schematic diagram showing the coaxial outer sleeve assembly of this utility model being assembled with the puncture needle assembly and the biopsy needle assembly respectively;

[0027] Figure 4 This is a schematic diagram of the coaxial inner needle core assembly of this utility model (handle cover is hidden);

[0028] Figure 5 This is a schematic diagram of the assembly and installation of the coaxial inner needle core assembly and the coaxial outer tube assembly of this utility model (handle cover is hidden);

[0029] Figure 6 This is a cross-sectional schematic diagram of the needle body portion after the coaxial inner needle core assembly and coaxial outer tube assembly of this utility model are assembled and installed.

[0030] Figure 7 This is a circuit example diagram of the DC-AC module of this utility model;

[0031] Figure 8 A schematic diagram of the functional modules of the energy generation component;

[0032] Figure 9 This is a schematic diagram of the working state of a biopsy needle kit with hemostasis function.

[0033] Explanation of reference numerals in the attached figures:

[0034] 1-Coaxial inner needle core assembly; 101-Coaxial inner needle core; 102-Handle; 1021-Outer tube socket; 1022-Energy generating assembly; 103-Inner insulation layer; 2-Coaxial outer tube assembly; 201-Coaxial outer tube 201; 202-Outer tube plug; 203-Outer insulation layer; 3-Biopsy needle assembly; 4-Puncture needle assembly. Detailed Implementation

[0035] The following specific examples illustrate the implementation of this utility model. Those skilled in the art can easily understand other advantages and effects of this utility model from the content disclosed in this specification. This utility model can also be implemented or applied through other different specific embodiments, and various details in this specification can be modified or changed based on different viewpoints and applications without departing from the spirit of this utility model. It should be understood that the terms "center," "longitudinal," "lateral," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model. Furthermore, the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Thus, features defined with "first," "second," etc., may explicitly or implicitly include one or more of that feature. In the description of this utility model, unless otherwise stated, "a plurality of" means two or more.

[0036] It should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to fixed connections, detachable connections, or integral connections; they can refer to mechanical connections or electrical connections; they can refer to direct connections or indirect connections through an intermediate medium; and they can refer to the internal connection between two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0037] Biopsy is the gold standard for tumor pathological diagnosis and is widely used in clinical practice. Traditional biopsy needles obtain tissue samples through mechanical cutting, but this method is prone to bleeding, especially for biopsies of special sites such as the liver and kidneys, where the risk of bleeding is even higher and may even endanger the patient's life.

[0038] Biopsies are categorized into bone biopsies, tissue biopsies, and cytological biopsies. For solid tumors, tissue biopsies are generally used for pathological diagnosis. Solid tumors include those in the liver, lungs, kidneys, prostate, and thyroid, among others. The principle of a tissue biopsy typically involves using spring force to rapidly cut the tissue. A typical tissue biopsy needle consists of a core and a syringe. The core usually has a sampling groove (1001), while the syringe is primarily used for rapid tissue cutting, leaving the tissue in the sampling groove (1001). Biopsy needles are available in various sizes, ranging from large (7G, 9G, 12G) to smaller (16G, 18G, 20G), etc. Because of the mechanical cutting and puncture procedures, bleeding is the most frequent complication during biopsies. In normal circumstances, this bleeding can be easily stopped by clotting. However, in some special organs, special sites, or in some special patients, such as those with coagulation disorders, massive bleeding can easily occur. In such cases, biopsies cannot be performed normally. Clinically, there are some methods to address this type of bleeding, such as using radiofrequency or microwave to achieve needle tract hemostasis. However, this is considered emergency medical care, which is expensive and complex.

[0039] Example

[0040] See Figures 1-3 Therefore, this embodiment provides a biopsy needle kit with hemostasis function, including:

[0041] The coaxial inner needle core assembly 1 includes a coaxial inner needle core 101 and a handle 102. The coaxial inner needle core 101 is fixedly connected to the handle 102. An energy generating component 1022 is disposed inside the handle 102. An inner insulating layer 103 is disposed on the outer periphery of the coaxial inner needle core 101. The distal end of the coaxial inner needle core 101 extends out of the inner insulating layer 103 to form a first electrode. The proximal end of the coaxial inner needle core 101 is electrically connected to the energy generating component 1022.

[0042] The coaxial outer tube assembly 2 includes a coaxial outer tube 201 and an outer tube plug 202. An outer insulating layer 203 is provided on the outer periphery of the coaxial outer tube 201. The distal end of the coaxial outer tube 201 extends out of the outer insulating layer 203 to form a second electrode. In the hemostasis configuration, the coaxial inner needle core 101 is inserted into the coaxial outer tube 201 and the distal end of the coaxial inner needle core 101 extends out of the coaxial outer tube 201. The outer tube plug 202 is inserted into the handle 102. The proximal end of the coaxial outer tube 201 is electrically connected to the energy generating assembly 1022.

[0043] The biopsy needle assembly 3 is used to pass through the coaxial outer sleeve 201 to reach a predetermined position for biopsy sampling;

[0044] During hemostasis, the coaxial inner needle core 101 is inserted through the coaxial outer tube 201, and the energy generating component 1022 ablates and stops the bleeding of the puncture needle tract through the first electrode and the second electrode.

[0045] The technical solution of this embodiment uses a coaxial outer cannula assembly 2 to preserve the needle path and to form two electrodes with the coaxial inner needle core 101 for needle path ablation and hemostasis. Specifically, after sampling is completed, the sampling needle is withdrawn, while the coaxial outer cannula assembly 2 remains in the needle path to preserve it. The coaxial inner needle core 101 is then inserted into the cannula needle, easily replicating the needle path punctured during sampling. An appropriate current is supplied to the first and second electrodes via the energy generating assembly 1022, enabling tissue ablation and coagulation to avoid needle path bleeding. Because the portable energy generating assembly 1022 is housed within the handle 102, ablation and coagulation operations can be conveniently performed after biopsy sampling, preventing accidental bleeding.

[0046] Preferably, it also includes a puncture needle assembly 4, which is inserted into the coaxial outer sleeve 201 and the distal end of the puncture needle extends out of the distal end of the coaxial outer sleeve 201 to puncture to the target position.

[0047] The technical solution of this embodiment also includes a specially configured puncture needle assembly 4, see [link to documentation]. Figure 9 The puncture needle assembly 4 is used to perform punctures to reach the target position after being assembled with the coaxial outer sheath assembly 2.

[0048] See Figure 6 Preferably, the coaxial inner needle core 101 is closed at its distal end, and a thermocouple sensor is provided at the distal end of the coaxial inner needle core 101. The thermocouple sensor collects the temperature of the distal end of the coaxial inner needle core 101 in real time. When the coaxial inner needle core 101 is inserted into the coaxial outer tube 201, the inner insulating layer 103 extends out of the distal end of the coaxial outer tube 201.

[0049] The technical solution of this embodiment sets the distal end of the coaxial inner needle core 101 in a closed state and sets a thermocouple sensor inside it, so as to collect the temperature of ablation and coagulation in real time, and prevent inadequate ablation and hemostasis or excessive ablation, which would cause excessive damage to the patient.

[0050] Preferably, the handle 102 is provided with an outer tube socket 1021, and the outer tube plug 202 is electrically connected to the handle 102 by plugging into the outer tube socket 1021.

[0051] The technical solution of this embodiment provides an outer tube plug 202 on the coaxial outer tube 201 and an outer tube socket 1021 on the handle 102. When the coaxial inner needle core assembly 1 and the coaxial outer tube assembly 2 are assembled, the structural and electrical connection is achieved through the outer tube plug 202 and the outer tube socket 1021, which makes the installation convenient, stable and quick.

[0052] See Figure 4 , Figure 5 , Figure 8 Preferably, the energy generating component 1022 includes a 12V polymer lithium battery, a high-frequency drive module, a DC-AC module, and a boost transformer. The 12V polymer lithium battery converts direct current into alternating current through the DC-AC module. The boost transformer further boosts the converted alternating current and ablates and stops bleeding through the puncture needle tract via the first electrode and the second electrode.

[0053] This embodiment provides an energy generating component 1022. A DC-AC module converts the direct current from a 12V polymer lithium battery into alternating current. A step-up transformer increases the low-voltage alternating current to a higher voltage level to meet the voltage requirements for ablation and hemostasis. High-voltage discharge is applied to the puncture needle tract through the first and second electrodes, generating heat to achieve tissue coagulation and hemostasis. Using a polymer lithium battery as a power source provides a lightweight energy solution suitable for mobile medical environments or emergency situations. Simultaneously, the high-frequency drive module improves energy conversion efficiency and reduces energy loss. Due to the use of a specialized step-up transformer and electrode design, operational safety is ensured to a certain extent, reducing damage to surrounding tissues.

[0054] Preferably, the DC-AC module includes a half-bridge circuit and a resonant circuit. The input terminal of the half-bridge circuit is connected to the high-frequency drive module to provide a drive signal to the DC-AC module. The output terminal of the half-bridge circuit is connected to the input terminal of the resonant circuit, and the output terminal of the resonant circuit is connected to the step-up transformer.

[0055] A half-bridge circuit converts direct current (DC) to alternating current (AC) by alternately turning two switching elements (such as transistors) on and off. It has a simple structure, low cost, and can effectively control the waveform of the output voltage. A resonant circuit, typically composed of an inductor and a capacitor, is used to improve circuit efficiency and stability. In DC-AC conversion, resonant circuits can help reduce switching losses, improve energy conversion efficiency, and reduce electromagnetic interference.

[0056] See Figure 7Preferably, in some embodiments, the half-bridge circuit includes a first MOSFET, a second MOSFET, a first Zener diode, a first resistor, a second resistor, a second Zener diode, a third resistor, and a fourth resistor. The first terminal of the first resistor is connected to the signal terminal of the high-frequency drive module. The second terminal of the first resistor is connected to the gate (G) of the first MOSFET. The drain (D) of the first MOSFET is connected to the power supply. The source (S) of the first MOSFET is connected to the drain (D) of the second MOSFET. The first resistor and the first Zener diode are connected in reverse parallel. The anode of the first Zener diode is connected to the resonant circuit through the second resistor. The gate (G) of the second MOSFET is connected to the second terminal of the third resistor. The first terminal of the third resistor is connected to the signal terminal of the high-frequency drive module. The third resistor and the second Zener diode are connected in reverse parallel. The anode of the second Zener diode is connected to the resonant circuit through the fourth resistor.

[0057] See Figure 7 Preferably, in some embodiments, the resonant circuit includes a first capacitor, a second capacitor, a third capacitor, a fourth capacitor, a fifth capacitor, and a vertical inductor. The first capacitor, the second capacitor, and the vertical inductor are connected in series. The third capacitor is connected in parallel with the first capacitor. The vertical inductor is connected to the fourth capacitor and the fifth capacitor connected in parallel. The first terminal of the fifth capacitor is connected to the first port of the step-up transformer, and the second terminal of the fifth capacitor is connected to the fourth port of the transformer U3.

[0058] Preferably, in some embodiments, the handle 102 is provided with an operation button for controlling the on / off state of the circuit of the energy generating component 1022 and a status indicator light for displaying the battery level in the energy generating component 1022.

[0059] Preferably, in some embodiments, the high-frequency drive signal output by the high-frequency drive module is greater than or equal to 480kHz.

[0060] This invention eliminates the need for a radiofrequency or microwave host during hemostasis. We integrate the functions required for biopsy hemostasis from a bulky radiofrequency (microwave) host into a disposable consumable, truly enabling biopsy and hemostasis to be completed in one procedure during outpatient surgery. This significantly reduces surgical time and costs while greatly improving surgical safety. This invention can be used for various tissue biopsies, especially for high-risk bleeding procedures such as liver cancer and kidney cancer biopsies, and has broad application prospects.

[0061] Furthermore, in the description of this application, "proximal" and "distal" are commonly used terms in the medical field. Specifically, "proximal" refers to the end closer to the operator, "proximal face" refers to the end face closer to the operator, "distal" refers to the end farther from the operator, and "distal face" refers to the end face farther from the operator.

[0062] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings, but the present invention is not limited to the above embodiments. Even if various changes are made to the present invention, if these changes fall within the scope of the claims of the present invention and their equivalents, they shall still fall within the protection scope of the present invention.

Claims

1. A biopsy needle kit with hemostatic function, characterized in that, include: A coaxial inner needle core assembly includes a coaxial inner needle core and a handle. The coaxial inner needle core is fixedly connected to the handle. An energy generating component is disposed inside the handle. An inner insulating layer is disposed on the outer periphery of the coaxial inner needle core. The distal end of the coaxial inner needle core extends out of the inner insulating layer to form a first electrode. The proximal end of the coaxial inner needle core is electrically connected to the energy generating component. A coaxial outer cannula assembly includes a coaxial outer cannula and an outer cannula plug. An outer insulating layer is provided on the outer periphery of the coaxial outer cannula. The distal end of the coaxial outer cannula extends out of the outer insulating layer to form a second electrode. In a hemostatic configuration, the coaxial inner needle core is inserted into the coaxial outer cannula and the distal end of the coaxial inner needle core extends out of the coaxial outer cannula. The outer cannula plug is inserted into the handle. The proximal end of the coaxial outer cannula is electrically connected to the energy generating component. A biopsy needle assembly is used to pass through the coaxial outer tube to reach a predetermined position for biopsy sampling. During hemostasis, the coaxial inner needle core is inserted into the coaxial outer tube, and the energy generating component ablates and stops the bleeding of the puncture needle tract through the first electrode and the second electrode.

2. The biopsy needle kit with hemostatic function as described in claim 1, characterized in that, It also includes a puncture needle assembly, which is inserted into the coaxial sheath and the distal end of the puncture needle extends beyond the distal end of the coaxial sheath to puncture to the target location.

3. The biopsy needle kit with hemostatic function as described in claim 2, characterized in that, The coaxial inner needle core is closed at its distal end, and a thermocouple sensor is provided at the distal end of the coaxial inner needle core. The thermocouple sensor collects the temperature of the distal end of the coaxial inner needle core in real time. When the coaxial inner needle core is inserted into the coaxial outer tube, the inner insulating layer extends out of the distal end of the coaxial outer tube.

4. The biopsy needle kit with hemostatic function as described in claim 3, characterized in that, The handle is provided with an outer tube socket, and the outer tube plug is connected to the handle through the outer tube socket to achieve electrical connection.

5. The biopsy needle kit with hemostatic function as described in claim 1 or 2, characterized in that, The energy generating component includes a 12V polymer lithium battery, a high-frequency drive module, a DC-AC module, and a step-up transformer. The 12V polymer lithium battery converts direct current into alternating current through the DC-AC module. The step-up transformer further boosts the converted alternating current and ablates and stops bleeding through the puncture needle tract via the first electrode and the second electrode.

6. The biopsy needle kit with hemostatic function as described in claim 5, characterized in that, The DC-AC module includes a half-bridge circuit and a resonant circuit. The input terminal of the half-bridge circuit is connected to the high-frequency drive module to provide a drive signal to the DC-AC module. The output terminal of the half-bridge circuit is connected to the input terminal of the resonant circuit, and the output terminal of the resonant circuit is connected to the step-up transformer.

7. The biopsy needle kit with hemostatic function as described in claim 6, characterized in that, The half-bridge circuit includes a first MOSFET, a second MOSFET, a first Zener diode, a first resistor, a second resistor, a second Zener diode, a third resistor, and a fourth resistor. The first terminal of the first resistor is connected to the signal terminal of the high-frequency drive module. The second terminal of the first resistor is connected to the gate (G) of the first MOSFET. The drain (D) of the first MOSFET is connected to the power supply. The source (S) of the first MOSFET is connected to the drain (D) of the second MOSFET. The first resistor and the first Zener diode are connected in reverse parallel. The anode of the first Zener diode is connected to the resonant circuit through the second resistor. The gate (G) of the second MOSFET is connected to the second terminal of the third resistor. The first terminal of the third resistor is connected to the signal terminal of the high-frequency drive module. The third resistor and the second Zener diode are connected in reverse parallel. The anode of the second Zener diode is connected to the resonant circuit through the fourth resistor.

8. The biopsy needle kit with hemostatic function as described in claim 7, characterized in that, The resonant circuit includes a first capacitor, a second capacitor, a third capacitor, a fourth capacitor, a fifth capacitor, and a vertical inductor. The first capacitor, the second capacitor, and the vertical inductor are connected in series. The third capacitor is connected in parallel with the first capacitor. The vertical inductor is connected to the fourth capacitor and the fifth capacitor connected in parallel. The first terminal of the fifth capacitor is connected to the first port of the step-up transformer, and the second terminal of the fifth capacitor is connected to the fourth port of the transformer U3.

9. The biopsy needle kit with hemostatic function as described in claim 5, characterized in that, The handle is equipped with operation buttons for controlling the on / off state of the energy generating component circuit and status indicator lights for displaying the battery level in the energy generating component.

10. The biopsy needle kit with hemostatic function as described in claim 5, characterized in that, The high-frequency drive module outputs a high-frequency drive signal greater than or equal to 480kHz.

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